Image processing apparatus, image processing method, and program

ABSTRACT

An image processing apparatus includes a calculation unit configured to calculate information indicating similarity among a plurality of tomographic images, and a generation unit configured to generate a tomographic image from the plurality of tomographic images based on the calculated information indicating similarity.

TECHNICAL FIELD

The present invention relates to a technique for the enhancement ofimage quality of a tomographic image in an eye portion.

BACKGROUND ART

A tomographic imaging apparatus for the eye portion such as an opticalcoherence tomography (hereinafter referred to as OCT) is usable tothree-dimensionally observe a state inside a retinal layer. In recentyears, the tomographic imaging apparatus has attracted attention becauseit is useful in accurately diagnosing disease.

In an ophthalmologic diagnosis, there can be used a volume image forgrasping the state of the entire retinal layer and a high image-qualitytwo-dimensional tomographic image for grasping a layer which is notimaged on a low image-quality tomographic image. The volume image refersto aggregation of the two-dimensional tomographic images.

The image quality of the tomographic image acquired by the OCT dependson the strength of near infrared light incident on a retina. For thisreason, the strength of the light with which the retina is irradiatedneeds to be increased to improve the image quality of the tomographicimage. However, from the viewpoint of safety, the strength of the lightwith which the retina can be irradiated is limited. This requires thehigh image-quality tomographic image to be generated while the retina isbeing irradiated with near infrared light within the unquestionablestrength of the light from the viewpoint of safety. To meet such arequirement, Japanese Patent Application Laid-Open No. 2008-237238discusses a technique in which two-dimensional captured tomographicimages are superposed on each other to generate a noiseless sectionalimage.

In Japanese Patent Application Laid-Open No. 2008-237238, however, aplurality of tomographic images are merely subjected to arithmetic mean.For this reason, in a case where correlation is low between the addedtomographic images, a reduction in diagnosis information can beincreased. In particular, since involuntary eye movement occurs in eyes,the entire areas of adjacent images are not always similar.

SUMMARY OF INVENTION

The present invention is directed to an improvement in quality of atomographic image.

According to an aspect of the present invention, an image processingapparatus includes calculation means configured to calculate informationindicating similarity among a plurality of tomographic images, andgeneration means configured to generate a tomographic image from theplurality of tomographic images based on the calculated informationindicating similarity.

Further features and aspects of the present invention will becomeapparent from the following detailed description of exemplaryembodiments with reference to the attached drawings.

BRIEF DESCRIPTION OF DRAWINGS

The accompanying drawings, which are incorporated in and constitute apart of the specification, illustrate exemplary embodiments, features,and aspects of the invention and, together with the description, serveto explain the principles of the invention.

FIG. 1 illustrates a configuration of an image processing systemaccording to a first exemplary embodiment of the present invention.

FIG. 2A is a flow chart illustrating a tomographic image capturingprocess in an image processing apparatus according to the firstexemplary embodiment.

FIG. 2B is a flow chart illustrating the tomographic image capturingprocess in the image processing apparatus according to the firstexemplary embodiment.

FIG. 3A is a diagram for describing superposition image generationprocessing.

FIG. 3B is a diagram for describing the superposition image generationprocessing.

FIG. 3C is a diagram for describing the superposition image generationprocessing.

FIG. 4 is a diagram for describing superposition areas.

FIG. 5A is a diagram for describing superposition determinationprocessing.

FIG. 5B is a diagram for describing the superposition determinationprocessing.

FIG. 5C is a diagram for describing the superposition determinationprocessing.

FIG. 6 is a block diagram illustrating a configuration of an imageprocessing system according to a second exemplary embodiment of thepresent invention.

FIG. 7A is a flow chart illustrating a tomographic image capturingprocess in an image processing apparatus according to the secondexemplary embodiment.

FIG. 7B is a flow chart illustrating the tomographic image capturingprocess in the image processing apparatus according to the secondexemplary embodiment.

FIG. 8A is a diagram for describing superposition areas.

FIG. 8B is a diagram for describing the superposition areas.

FIG. 8C is a diagram for describing the superposition areas.

DESCRIPTION OF EMBODIMENTS

Various exemplary embodiments, features, and aspects of the inventionwill be described in detail below with reference to the drawings.

FIG. 1 illustrates an image processing system 100 including an imageprocessing apparatus 110 according to a first exemplary embodiment ofthe present invention. As illustrated in FIG. 1, the image processingsystem 100 is configured such that the image processing apparatus 110 isconnected to a tomographic imaging apparatus 120 via an interface.

The tomographic imaging apparatus 120 is the one that captures atomographic image of an eye portion and is comprised of a time-domainOCT or a Fourier-domain OCT, for example. The tomographic imagingapparatus 120 is a known apparatus, so that the detailed descriptionthereof is omitted herein.

The image processing apparatus 110 includes an acquisition unit 111, astorage unit 112, an image processing unit 113, and a display controlunit 114.

The acquisition unit 111 acquires a tomographic image captured by thetomographic imaging apparatus 120 and stores the captured tomographicimage in the storage unit 112. The image processing unit 113 generates anew two-dimensional tomographic image from the tomographic images storedin the storage unit 112. The display control unit 114 performs controlfor displaying the processed image on a monitor (not illustrated).

A plurality of places may be sequentially scanned. As an example,however, FIG. 3A illustrates a schematic diagram of two-dimensionaltomographic image groups in a macula lutea portion in which thetomographic imaging apparatus 120 continues repetitively scanning andimaging almost the same place. A direction in which scanning isperformed with a measuring beam to capture a two-dimensional tomographicimage is referred to as a main scanning direction. A directionorthogonal to the main scanning direction is referred to as asub-scanning direction.

In general, the tomographic imaging apparatus 120 performs imaging inthe main scanning direction while shifting the measuring beam in thesub-scanning direction. In other words, the present exemplary embodimentis also adaptable to a case where the measurement light is shifted inthe sub-scanning direction.

In FIG. 3A, coordinate axes x and y and time base t are provided. FIG.3A also illustrates two-dimensional tomographic images T₁ to Tn in themacula lutea portion imaged at different points of time. In other words,the two-dimensional tomographic image group is formed of aggregation ofthe two-dimensional tomographic images in which almost the same place iscaptured.

The enhancement of image quality refers to the improvement of S/N ratio.The improvement of image quality refers to the improvement of S/N ratio.

The processing by the image processing apparatus 110 according to thepresent exemplary embodiment is described below with reference to a flowchart in FIGS. 2A and 2B.

In step S201, a control unit (not illustrated) controls the tomographicimaging apparatus 120 to capture a retinal layer. A position in thedirection of depth (a direction z in FIG. 3A) being a direction in whichthe retina is irradiated with the measuring beam and the direction ofplane (a direction x in FIG. 3A) orthogonal to the direction z isadjusted. The alignment of position of direction of depth corresponds tothe alignment of position of a coherent gate for acquiring a tomographicimage.

In step S201, the control unit (not illustrated) performs adjustment toa position suitable for imaging the retinal layer. In step S202, animaging instruction unit (not illustrated) issues instructions to startimaging.

In step S203, when an operator issues instructions for imaging, thecontrol unit (not illustrated) repetitively scans almost the same placeto capture a plurality of tomographic images.

The control unit (not illustrated) also has a function to adjust thedistance of movement in the sub-scanning direction.

In step S204, the image processing unit 113 generates a newtwo-dimensional tomographic image using the two-dimensional tomographicimage group stored in the storage unit 112. The generation of thetwo-dimensional tomographic image whose image quality is enhanced isdescribed below with reference to FIG. 2B.

In step S210, a first alignment unit 115 aligns the two-dimensionaltomographic images with one another. The alignment is performed suchthat an evaluation function indicating the similarity of twotwo-dimensional tomographic images, for example, is previously definedand the tomographic image is deformed so that the value of theevaluation function is maximized A method for performing evaluation by apixel value (a method for performing evaluation using the correlationcoefficient of equation (1), for example), is used as the evaluationfunction. Processing in which translation or rotation is performed usingaffine transformation or magnification rate is changed is used asprocessing for deforming an image. The alignment may be performed on thebasis of a feature point. A feature portion such as a retinal layer or alesion is extracted from the two-dimensional tomographic image, forexample. Since an internal limiting membrane, nerve fiber layer, visualcell inner-outer segment junction, and stratum pigmenti retinae are highin luminance and the boundary of the layer is high in contrast, thedetection results on the layers and the feature portions are used toperform the alignment.

A deformation parameter is calculated at which the evaluation functionis maximized while deforming the two-dimensional tomographic image toalign the two-dimensional tomographic images with one another. If thenumber of two-dimensional tomographic images to be superposed is N, N-1two-dimensional tomographic images are aligned with the two-dimensionaltomographic image serving as a reference.

In step S211, a determination unit 117 determines A-scan imagessuperposed in units of the corresponding A-scan images. This process isdescribed below with reference to FIG. 4. Two-dimensional tomographicimages Ti′ and Ti+1′ captured at different points of time are aligned instep S210. Aij′ and A(i+1)j′ represent the corresponding A-scan imagesin the aligned two-dimensional tomographic images Ti′ and Ti+1′. TheA-scan image in the present exemplary embodiment refers to one pixel rowparallel to the direction of the z axis in FIG. 4.

The A-scan image is the one that agrees with the direction in which ameasuring beam is incident. Each of the A-scan images acquired from thesame place has almost the same image information. For this reason, evenif the entire two-dimensional tomographic images are low in similaritydue to involuntary eye movement, data mutually high in similarity canexist in the A-scan images of different two-dimensional tomographicimages.

Image areas Rij′ and R(i+i)j′ each represent an area of +− .alpha. inthe direction of the x axis with the A-scan images Aij′ and A(i+1)j′ asa center. A calculation unit 116 calculates a similarity between theA-scan images in the image areas Rij′ and R(i+1)j′ with the A-scan imageas a center. In a case where a reference area for determiningsuperposition is taken as the area Rij′, the calculation unit 116calculates a similarity between the areas corresponding to all of theareas R1j′ to Rnj′. A formula using a correlation coefficient as anevaluation function indicating a similarity between the A-scan images isexpressed by an expression (1).

$\begin{matrix}\left\lbrack {{Math}.\mspace{14mu} 1} \right\rbrack & \; \\\frac{\underset{S}{\int\int}\left( {{f\left( {x,y} \right)} - \overset{\_}{f}} \right)\left( {{g\left( {x,y} \right)} - \overset{\_}{g}} \right){x}{y}}{\sqrt{\underset{S}{\int\int}\left( {{f\left( {x,y} \right)} - \overset{\_}{f}} \right)^{2}{x}{y}\underset{S}{\int\int}\left( {{g\left( {x,y} \right)} - \overset{\_}{g}} \right)^{2}{x}{y}}} & (1)\end{matrix}$

In FIG. 4, where the area Rij′ is taken as f(x, y) and the area R(i+1)j′is taken as g(x, y),

f and g  [Math.2]

represent the averages of areas f(x, y) and g(x, y), respectively.

The determination unit 117 selects an area used for superposition foreach area. The processing by the determination unit 117 is describedbelow with reference to FIGS. 5A to 5C. FIGS. 5A to 5C illustrateexamples of results obtained by the calculation unit 116 calculating thesimilarity between areas.

The abscissa represents numbers 1 to N of the captured two-dimensionaltomographic images. The ordinate signifies a similarity between areference area and other areas in the two-dimensional tomographicimages. FIG. 5A illustrates a method (a) for setting a threshold Th toselect an area whose similarity exceeds a predetermined value. FIG. 5Billustrates a method (b) for selecting top M images of similarity whenthe areas in FIG. 5A are sorted in descending order of similarity. FIG.5C illustrates a method (c) for representing rates of change ofsimilarity after the sorting process by a line graph when the areas inFIG. 5A are subjected to a sorting process in descending order ofsimilarity. Here is illustrated an example where images are selectedbefore the rate of change of similarity is significantly decreased. Morespecifically, the similarity at which the rate of change of similarityafter the sorting process shows the predetermined value is obtained toselect the area whose value exceeds the obtained similarity.

In addition to the above, there is another method (d) for observing therate of change of similarity without conducting the sort process. Thecalculation unit 116 stops calculating an evaluation value if thesimilarity is lower than a predetermined value. An image in which theevaluation value is higher than the predetermined value and thecalculation thereof is still being performed is selected.

For the method (a) using the threshold, the area where the evaluationvalue is lower is not used for superposition, so that only the areaswhere the valuation value is high can be superposed.

This is suitable for the case where the movement distance per unit timein the subscanning direction is small. This is because the method has aneffect in which an organization structure is changed a little but theimage of the area which is greatly different in organization structureand is produced by unique movement or blinking of an eye is notselected.

For the method (b) selecting the fixed number M of images, the number ofpieces of data subjected to superposition average processing in units ofan image is not dispersed. The number of pieces of data subjected tosuperposition average processing in units of an A-scan image is also notdispersed. The extent that a noise is reduced can be leveled, so thatthe method (b) is suitable for the case where the image quality isequalized.

The method (c) using a rate of change is characterized in that the areassimilar to each other can be selected even in the case where the imagequality is inferior as a whole due to illness and the similarity is lowas a whole.

The method (d) is suitable also for the case where the movement distanceper unit time in the sub-scanning direction is large. This is becausethe calculation unit 116 can be prevented from unnecessarily calculatingan evaluation value due to the reason that a displacement in thesub-scanning direction exceeding the predetermined value makes theorganization structure of retina different. In other words, a change inthe organization structure can also be recognized by observing the rateof change.

As described above, the area where superposition is performed based onthe evaluation value is selected in each area. For this reason, in thecase where the retinal layer is deformed due to the involuntary eyemovement in the two-dimensional tomographic image or in an area wherethe image quality is partially lowered due to blink or shading is notused for superposition, the image quality of a newly generated image isenhanced.

The determination unit 117 performs processing of combining the abovemethods (a) to (d) according to the movement distance per unit time inthe sub-scanning direction. For example, in the case where the movementdistance is shorter than a predetermined value, the processing of themethod (a) or (b) is used. In the case where the movement distanceexceeds the predetermined value, the processing of the method (c) or (d)is used. A combination of the methods (a) and (d) can perform theprocessing attaching importance to speed. A combination of the methods(b) and (d) can perform the processing attaching importance to imagequality.

In step S212, a generation unit 118 performs superposition processing.The superposition of two A-scan images is described below. FIG. 3B is adiagram illustrating processing in which the two-dimensional tomographicimages are processed in units of the A-scan image to generate onetwo-dimensional tomographic image as a composite image. In other words,an addition average processing of the A-scan images positioned ondifferent two-dimensional tomographic images captured at differentpoints of time is described as an example. FIG. 3C illustrates ahigh-quality two-dimensional tomographic image generated by performingthe addition average processing using M pixels (two pixels in theexample) for each pixel. In FIG. 3C, Aij″ is a new A-scan imagecalculated by performing the addition average processing of thecorresponding A-scan images.

In FIG. 3B, Ti′ and Ti+1′ represent two-dimensional tomographic imagesin which the same cross section is captured at different points of time.Aij′ and A(i+1)j′ represent A-scan images in the respective tomographicimages Ti′ and Ti+1′. The generation unit 118 performs the additionaverage processing of the A-scan images Aij′ and A(i+1)j′ to calculatethe A-scan image Aij″ in FIG. 3C. The generation processing of ahigh-quality two-dimensional tomographic image (composite image) is notlimited to the addition average processing. A medium value calculationprocessing or a weighted addition average processing may be used. All ofthe A-scan images (Ai1′ to Aim′) of the reference image Ti′ aresubjected to these processing. In the weighted addition averageprocessing, for example, the aforementioned similarity is used as weightof addition.

Although the present exemplary embodiment describes the case where anarea where a similarity is calculated is taken as Rij′ and thesuperposition processing is performed on Aij′ (in units of the A-scanimage), the present invention is not limited to the above exemplaryembodiment. The superposition processing may be performed in units ofthe area where a similarity is calculated, for example. Alternatively,the superposition processing may be performed on two-dimensionaltomographic images. Furthermore, the superposition processing may beperformed such that a similarity is calculated in units of the A-scanimage with .alpha. as 0(Rij′=Aij′ at .alpha.=0).

In step S205, the display control unit 114 displays the high-qualitytwo-dimensional tomographic image generated in step S204 on a displayunit (not illustrated). Although the above example describes that almostthe same retinal area is scanned with the area fixed where the measuringbeam of the tomographic imaging apparatus 120 is used for scanning, asdescribed above, the present invention is applicable even if the entireretina is sequentially scanned.

As is understood from the above description, in the present exemplaryembodiment, a similarity between the areas in a plurality of the alignedtwo-dimensional tomographic images is calculated using the correspondingA-scan images and a peripheral area and the area used for thesuperposition processing is determined in units of area. This allows ahigh-quality two-dimensional tomographic image to be generated becausethe area used for the superposition processing is determined in units ofa partial area even in the case where the entire images are aligned butthe retinal layer in the two-dimensional tomographic image is deformeddue to involuntary eye movement.

According to the present exemplary embodiment, a high-qualitytwo-dimensional tomographic image can be acquired even in the case wherethe two-dimensional tomographic image is deformed due to involuntary eyemovement. The high-quality image refers to an image whose S/N ratio ismade better than an image captured once. Alternatively, the high-qualityimage refers to an image in which the amount of information required fordiagnosis is increased.

In the first exemplary embodiment, a similarity between the areas in thealigned two-dimensional tomographic images is calculated using thecorresponding A-scan images and a peripheral area and the area used forthe superposition processing is determined in units of area. In a secondexemplary embodiment of the present invention, an area where theevaluation value is high in a neighbor area is searched in the alignedtwo-dimensional tomographic images using the A-scan images and aperipheral area to perform the superposition processing. According tothe second exemplary embodiment, a general alignment is performed usinga general characteristic, and alignment is performed using a localcharacteristic. Thereafter, the superposition processing is performed.

FIG. 6 is a block diagram illustrating a configuration of an imageprocessing system 600 including an image processing apparatus 610according to the second exemplary embodiment. As illustrated in FIG. 6,the image processing apparatus 610 includes the acquisition unit 111,the storage unit 112, an image processing unit 613, and the displaycontrol unit 114. The units excluding the image processing unit 613 havefunctions similar to those in the first exemplary embodiment, so thatthe description thereof is omitted herein.

In the image processing unit 613, a second alignment unit 619 performs alocal alignment using the A-scan images and a peripheral area.

The processing by the image processing apparatus 610 according to thepresent exemplary embodiment is described below with reference to FIGS.7A and 7B and FIGS. 8A to 8C. The steps other than step S704 are similarto steps S201 to S203 and step S205 in the first exemplary embodiment,so that the description thereof is omitted herein.

In step S704, the image processing unit 613 performs a general alignmentand a local alignment to perform image superposition processing, thusgenerating a high-quality two-dimensional tomographic image. Thegeneration processing of the high-quality two-dimensional tomographicimage is described below with reference to FIG. 7B.

In step S710, the first alignment unit 115 aligns two-dimensionaltomographic images with each other. The processing is similar to stepS210 of the first exemplary embodiment, so that the description thereofis omitted herein.

In step S711, the two-dimensional tomographic images generally alignedin step S710 are aligned in units of the corresponding A-scan image toperform a local alignment. The processing is described below withreference to FIG. 8A. Ti′ and Ti+1′ represent images in which the samecross section is captured at different points of time, which are thetwo-dimensional tomographic images aligned in step S701. Aij′ representsan A-scan image in the two-dimensional tomographic image Ti′. The shadedarea Rij″ represents a range of +− .alpga. in the direction of the xaxis with the A-scan image Aij′ as a center. R(i+1)j″ represents arectangular area corresponding to the range Rij″ in the two-dimensionaltomographic image Ti+1′. S(i+1)j″ represents a search range for movingthe rectangular area R(i+1)j″. If the reference A-scan image is taken asAij′ and an area where a similarity is calculated is taken as Rij″, therectangular area R(i+1)j″ in the search range S(i+1)j′ is scanned, andthe calculation unit 116 calculates an evaluation value.

The calculation unit 116 calculates the correlation of pixel valuesbetween the areas Rij″ and R(i+1)j″, and the determination unit 117evaluates the evaluation value. Alternatively, the boundary of a retinallayer is detected to detect the thickness of the layer. The calculationunit 116 calculates the evaluation value of similarity using thethickness of the layer. FIG. 8B illustrates how the similarity isevaluated using the thickness of the layer. FIG. 8B illustrates theboundary of a retinal layer (an internal limiting membrane L1 and astratum pigmenti retinae L2) in the search range S(i+1)j″ and thethickness values 1 to 3 of the layer. The thickness of the layer on eachA-scan image is acquired in the rectangular area R(i+1)j″. Thecalculation unit 116 compares the thickness of the layers in the areasRij″ and R(i+1)j″ with each other to calculate the evaluation value. Thelayer used for calculating the thickness of the layer is not limited tothe above-mentioned layer. Other boundaries of a layer such as a nervefiber layer or a visual cell inner-outer segment junction may be used tocompare the thickness of the layer.

Although the superposition determination processing performed by thedetermination unit 117 is omitted in the present exemplary embodiment,it may be determined whether superposition is performed based onsimilarity after alignment is performed in units of the A-scan image asis the case with the first exemplary embodiment.

In step S712, the generation unit 118 performs processing forsuperposing the corresponding A-scan images with each other. Morespecifically, the generation unit 118 performs superposition processingbetween the A-scan image positioned at the center of the rectangulararea R(i+l)j″ where the evaluation value is maximized and the referenceA-scan image Aij′.

In the present exemplary embodiment, the area Rij″ is set as arectangular area of the range of +− .alpha. with the position of theA-scan image as a center. As a method for setting the area Rij″, .alpha.may not be fixed, but may be dynamically changed according to an imagefeature of the retinal layer captured in the two-dimensional tomographicimage. FIG. 8C illustrates an example of setting the area. For example,in a case where the retinal layer is planar, the range of .alpha. is setwide (R(i+l)j″). In a case where the retinal layer is curved and acharacteristic place exists in the two-dimensional tomographic image (alarge number of vertical and horizontal edges exist), the range of.alpha. is set narrow (R(i+1)k″). The range of an area may be changedfor each case according to the image feature or may be changed in unitsof the A-scan image in one two-dimensional tomographic image.

As is apparent from the above description, in the present exemplaryembodiment, an area where an evaluation value is high in a neighbor areais searched in the aligned two-dimensional tomographic images using theA-scan images and a peripheral area to perform the superpositionprocessing. This allows a high-quality two-dimensional tomographic imageto be generated because the local alignment is performed even in thecase where the entire images are aligned but the retinal layer in thetwo-dimensional tomographic image is deformed due to involuntary eyemovement.

The foregoing exemplary embodiments realize the present invention as animage processing apparatus. The exemplary embodiments of the presentinvention, however, are not limited only to the image processingapparatus. The present invention can be realized as software operatingon a computer. A central processing unit (CPU) of the image processingapparatus controls the entire computer using computer programs and datastored in a RAM and a ROM. The CPU also controls the execution ofsoftware programs corresponding to the units of the image processingapparatus to realize the functions of the units.

While the present invention has been described with reference toexemplary embodiments, it is to be understood that the invention is notlimited to the disclosed exemplary embodiments. The scope of thefollowing claims is to be accorded the broadest interpretation so as toencompass all modifications, equivalent structures, and functions.

This application claims priority from Japanese Patent Application No.2010-131257 filed Jun. 8, 2010, which is hereby incorporated byreference herein in its entirety.

1. An image processing apparatus comprising: calculation meansconfigured to calculate information indicating similarity among aplurality of tomographic images; and generation means configured togenerate a tomographic image from the plurality of tomographic imagesbased on the calculated information indicating similarity.
 2. The imageprocessing apparatus according to claim 1, wherein the calculation meanscalculates similarity among a tomographic image as reference and otherdifferent tomographic images, wherein the image processing apparatusfurther comprises determination means configured to determine atomographic image used for generation by the generation means from theplurality of tomographic images based on the calculated informationindicating similarity, and wherein, if a movement distance per unit timein a sub-scanning direction is less than a predetermined value incapturing the plurality of tomographic images, the determination meansselects a tomographic image the similarity of which exceeds apredetermined value, and if the movement distance per unit time in thesub-scanning direction is equal to or more than the predetermined valuein capturing the plurality of tomographic images, the determinationmeans sorts the similarities of the plurality of tomographic images andselects a tomographic image based on a rate of change of the sortedsimilarities.
 3. The image processing apparatus according to claim 1,wherein the calculation means calculates information indicatingsimilarity among partial areas of the plurality of tomographic images,and wherein the generation means generates images in new partial areasfrom images in the partial areas of the plurality of tomographic images.4. The image processing apparatus according to claim 3, wherein thepartial area is a A-scan image, and wherein the generation means addsthe plurality of A-scan images to one another based on informationindicating similarity among the A-scan images to generate a new A-scanimage.
 5. The image processing apparatus according to claim 1, whereinthe generation means adds a plurality of two-dimensional tomographicimages whose value indicating the similarity is higher than apredetermined value to one another to generate a tomographic image. 6.The image processing apparatus according to claim 1, wherein thegeneration means generates a new tomographic image from a fixed numberof tomographic images whose value indicating the similarity is higherthan a predetermined value.
 7. An image processing method comprising:acquiring a plurality of tomographic images; and generating a newtomographic image from the plurality of tomographic images based oninformation indicating similarity among the acquired plurality oftomographic images.
 8. A program for causing a computer to execute theimage processing method according to claim
 7. 9. An image processingapparatus comprising: calculation means configured to calculatesimilarity among A-scan images acquired from respective differenttwo-dimensional tomographic images; determination means configured todetermine A-scan images used for composition based on the similarity;and generation means configured to combine the A-scan images acquiredfrom respective different two-dimensional tomographic images based onthe determination to generate a composite image.